Multi-layer braided structures for occluding vascular defects

ABSTRACT

A collapsible medical device and associated methods of occluding an abnormal opening in, for example, a body organ, wherein the medical device is shaped from plural layers of a heat-treatable metal fabric. Each of the fabric layers is formed from a plurality of metal strands and the assembly is heat-treated within a mold in order to substantially set a desired shape of the device. By incorporating plural layers in the thus-formed medical device, the ability of the device to rapidly occlude an abnormal opening in a body organ is significantly improved.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a divisional of U.S. continuation-in-partapplication Ser. No. 11/820,841, filed on Jun. 21, 2007, which is acontinuation-in-part application Ser. No. 11/473,971, filed Jun. 23,2006, which is a continuation-in-part application Ser. No. 10/804,993,filed Mar. 19, 2004 all above applications of which are incorporatedherein by reference in their entireties.

BACKGROUND OF THE INVENTION

I. Field of the Invention

The present invention generally relates to intravascular devices fortreating certain medical conditions and, more particularly, relates to alow profile intravascular occlusion devices for treating congenitaldefects including Atrial and Ventricular Septal Defects (ASD and VSDrespectively), Patent Ductus Arteriosus (PDA) and Patent Foramen Ovate(PFO) as well as conditions that result from previous medical proceduressuch as Para-Valvular Leaks (PVL) following surgical valve repair orreplacement. The devices made in accordance with the invention areparticularly well suited for delivery through a catheter or the like toa remote location in a patient's heart or in analogous vessels or organswithin a patient's body.

II. Description of the Related Art

A wide variety of intra cardiac prosthetic devices are used in variousmedical procedures. For example, certain intravascular devices, such ascatheters and guide wires, are generally used simply to deliver fluidsor other medical devices to specific locations within the vascularsystem of a patient, such as a selective coronary artery. Other,frequently more complex, devices are used in treating specificconditions, such as devices used in removing vascular occlusions or fortreating septal defects and the like.

In certain circumstances, it may be necessary to occlude a patient'svessel, such as to stop blood flow through an artery to a tumor or otherlesion. Presently, this is commonly accomplished simply by inserting,for example, Ivalon particles (a trade name for vascular occlusionparticles) and short sections of coil springs into a vessel at a desiredlocation. These “embolization agents” will eventually become lodged inthe vessel, frequently floating downstream of the site at which they arereleased before blocking the vessel. This procedure is often limited inits utility, in part, due to the inability to precisely position theembolization agents. These embolization agents are not commonly used asan intra cardiac occluding device.

Physicians may temporarily occlude a septal defect until the patientstabilizes enough for open-heart surgical procedures and have usedballoon catheters similar to that disclosed by Landymore et al. in U.S.Pat. No. 4,836,204. When using such a catheter, an expandable balloon iscarried on a distal end of a catheter. When the catheter is guided tothe desired location, the balloon is inflated with a fluid until itsubstantially fills the defect and becomes lodged therein. Resins, whichwill harden inside the balloon, such as an acrylonitrile, can beemployed to permanently fix the size and shape of the balloon. Theballoon can then be detached from the end of the catheter and left inplace. If the balloon is not filled enough, it will not be firmly lodgedin the septal defect and may rotate and loosen from the septal wall,thereby being released into the blood flowing from the right or leftventricular chamber. Overfilling the balloon is an equally undesirableoccurrence, which may lead to the rupture of the balloon and release ofresins into the patient's bloodstream.

Mechanical embolization devices, filters and traps have been proposed inthe past, representative examples of which are disclosed in King et al.,U.S. Pat. No. 3,874,388 (the '388 patent), Das, U.S. Pat. No. 5,334,217(the '217 patent), Sideris, U.S. Pat. No. 4,917,089 (the '089 patent)and Marks, U.S. Pat. No. 5,108,420 (the '420 patent). The '388, '217,'089, and '420 devices are typically pre-loaded into an introducer ordelivery catheter and are not commonly loaded by the physician duringthe medical procedure. During deployment of these devices, recaptureinto the delivery catheter is difficult if not impossible, therebylimiting the effectiveness of these devices.

Significantly, the size of these devices is inherently limited by thestructure and form of the device. When using occluding devices, such asin the above-identified '089, '388, '217, or '420 patent (plugs toocclude septal defects), the pressure and therefore the chance ofdislodgment of the device increases with the size of the defect.Consequently, these devices must have a very large retention skirtpositioned on each side of the defect. Oftentimes, the position of theseptal defect dictates the size of the retention skirt. In a membranoustype septal defect, it is difficult, if not impossible to be able toeffectively position the '388, '217, '089, or '420 device without atleast partially closing off the aorta. Also, these disclosed devicestend to be rather expensive and time-consuming to manufacture. Hence, itis desirable to provide a low profile device that is recoverable andretractable into the delivery system without increasing the overallthickness of the device. The desired device should also be made with arelatively small retention skirt so as to be positionable within amembranous type septal defect without closing off the aorta.

It the case of a membranous ventricular septal defect, if the centraldiameter of the occluder is exerting too much pressure on the septum,heart block may occur, and if the retention skirt is too large, it mayinterfere with the opening and closing of the aortic valve. Thestiffness required to retain the current devices in place against bloodpressure makes them more difficult to deliver. Hence, there is a needfor a low profile, easy to deliver device, that can be shaped forretention without blocking off the aorta or aortic valve and which isconformable without exerting excess pressure on tissue near conductivepathways.

It the case of PDA's, a smaller, lower profile device that can fitthrough a 4 French catheter potentially allows treatment of pre-matureinfants with a PDA. These patients are current sent to surgery becausethe use of coils to occlude the PDA, are not suitable due to the size ofthe PDA anatomy.

Also, the shape of the prior art devices (for example, squares,triangles, pentagons, hexagons and octagons) requires a larger contactarea, having corners, which extend to the free wall of the atria. Eachtime the atria contracts (approximately 100,000 times per day), internalwires within the prior art devices, such as described in the Das '217patent, are flexed, creating structural fatigue fractures inapproximately 30 percent of all cases. The sharp corners of thesedevices resulted in a high percentage of cardiac perforations and theywere, therefore, withdrawn from the market. Furthermore, the previousdevices require a 14-16 French introducing catheter, making itimpossible to treat children affected with congenital defects with thesedevices.

Accordingly, it would be advantageous to provide a reliable occlusiondevice which is both easy to deploy through a 4-7 French catheter andwhich can be accurately placed in a vessel or organ. It would also bedesirable to provide a low-profile recoverable device for deployment inan organ of a patient's body.

In the Kotula et al. U.S. Pat. No. 5,846,261, there is described areliable, low-profile, intra cardiac occlusion device which may beformed to treat, for example, Ventricular Septal Defects (VSD), AtrialSeptal Defects (hereinafter ASD), and Patent Ductus Arteriosus(hereinafter PDA). When forming these intravascular devices from aresilient metal fabric, a plurality of resilient strands exhibiting amemory property are provided, with the wires being formed by braiding tocreate a resilient material. This braided fabric is then deformed togenerally conform to a molding surface of a molding element and thebraided fabric is heat treated in contact with the surface of themolding element at an elevated temperature. The time and temperature ofthe heat treatment is selected to substantially set the braided fabricin its deformed state. After the heat treatment, the fabric is removedfrom contact with the molding element and it will substantially retainits shape in the deformed state. The braided fabric so treated definesan expanded state of a medical device, which can be deployed through acatheter into a channel in a patient's body.

Embodiments of the Kotula et al. invention provide specific shapes formedical devices, which may be made in accordance with that invention toaddress identified medical needs and procedures. The devices have anexpanded low-profile configuration and may include recessed clamps thatgather and hold the ends of the braided metal fabric to preventunraveling and that attach to an end of a delivery device or guide wire,allowing recovery of the device after placement. In use, a guidecatheter is positioned and advanced in a patient's body such that thedistal end of the catheter is adjacent a desired treatment site fortreating a physiological condition. A preselected medical device, madein accordance with the Kotula et al. invention and having apredetermined shape, is then collapsed by longitudinally stretching andis inserted into the lumen of the catheter. The device is urged throughthe catheter and out the distal end whereupon, due to its memoryproperty, it will tend to substantially return to its expanded, relaxedstate adjacent the treatment site. The guide wire or delivery catheteris then released from the clamp and removed.

In accordance with a first of these embodiments, a generally elongatemedical device has a generally tubular middle portion and a pair ofexpanded diameter portions, with one expanded diameter portionpositioned at either end of the middle portion. The length of the middleportion approximates the wall in which the thickness of the defect to beoccluded is formed. The center of at least one of the expanded diameterportions may be concentric with or offset relative to the center of themiddle portion, thereby allowing occlusion of a variety of septaldefects including membranous type ventricular septal defect, whileproviding a retention skirt of sufficient size to securely close theabnormal opening in the septum. As mentioned above, each braided end ofthe device is held together with a clamp. The clamps may be recessedinto the expanded diameter portion of the device, thereby reducing theoverall length dimension of the device and creating a low profileoccluder.

In another embodiment of the Kotula et al. invention described in the'261 patent, the medical device is generally bell-shaped, having anelongate body, a tapered first end, and a larger flanged second end. Thesecond end has a fabric disc which will be oriented generallyperpendicular to an axis of a channel when deployed therein. The clamps,which hold together the braided strand ends, are recessed toward thecenter of the “bell” providing a low-profile device having a reducedoverall height dimension.

The ability of the devices described in the Kotula et al. '261 patent toocclude abnormal openings in a vascular organ depend upon the pick sizeof the braided structure which, in turn, depends upon the number of wirestrands used in the braid. However, a practical limit exists on just howmany such strands can be braided. For example, if 72 bobbins are used onthe braiding machine, the resulting pick size is such that a prolongedperiod of time must elapse before total thrombosis takes place and bloodflow through the device is totally occluded. Even with 144 bobbins,blood flow is not immediately stemmed. If the pick size were effectivelyhalved by doubling the number of bobbins on the braiding machine to 288,occlusion would occur somewhat instantaneous upon placement of themedical device in the abnormal opening. However, the resulting braidingmachine becomes impractical from a size and cost standpoint.

As a way of reducing the time required to achieve total occlusion, theKotula et al. '261 patent teaches the concept of filling the interior ofthe medical device with an occluding fiber or an occluding fabric, suchas a polyester fabric. This occluding fiber material or fabric isgenerally hand sewn in place, which adds significantly to themanufacturing cost of the medical devices. Perhaps more importantly,adding polyester fiber or fabric in the interior of the deviceinterferes with the ability to reduce the effective diameter of thedevice upon stretching prior to loading the device into the lumen of adelivery catheter. It should be recognized that by reducing the size ofthe delivery catheter, it can be used with smaller patients.

Thus, a need exists for a way to form a collapsible medical device foroccluding abnormal openings in a vascular organ which provides rapidocclusion following delivery and placement thereof and which does notrequire the addition of an occluding fabric placed within the interiorof the medical device as taught by the prior art.

Another limitation of the bell-shaped occlusion device described in theKotula et al '261 patent regards its use in occluding a Patent DuctusArteriosus (PDA) This passage way between the pulmonary artery and theaorta is variable in diameter and length and the passageway is notalways perpendicular to the connected vessels. The design of thebell-shape occlusion device is such that the rim at one end of thedevice placed in the higher pressure aortic side may project into theaorta when the passage is not perpendicular to the aortic wall. Thebell-shaped design also does not accommodate passageway length and routevariation ideally and it is possible for the device to partially extrudeout of the PDA. A further limitation is that the device must bedelivered from the more difficult to reach pulmonary artery side of thePDA. This is due to the arterial sheath size being larger than thefemoral artery in young patients. For infants, there is a need for a PDAoccluder design that is low in profile that can be delivered through a 4French catheter that allows for a venous delivery in premature infantsand an arterial approach in premature infants weighing more than 1.5-2kg. The advantage of a venous approach for PDA closure is to potentiallytreat infants as small a 1 kg. The advantage of an arterial approach inslightly larger premature infants is that both angiography and deviceimplant can take place from a common access point in the femoral artery.

There is also a need for an improved occlusion device (occluder) forclosing the PDA that allows for: improved security of placement;improved accommodation of diameter, length, and pathway variation;minimal projection into the flow stream of the pulmonary and aorticarteries; and for improved ease of placement from the aortic side byfemoral artery access in addition to the previous pulmonary arteryaccess.

In treating damaged or diseased heart valves such as the mitral oraortic valve, it is often necessary to surgically repair or replace thevalve with a tissue or mechanical valve. These valves generally have afabric cuff surrounding the valve at the base. The surgeon uses sutureto sew tissue, adjacent the valve base, to the cuff to hold the valve inplace. For a number of reasons, the suture may occasionally pull outfrom weak tissue or suture may break or suture may not have been sewnideally. In any event this loss of connective tissue to the valve cuffresults in open holes (para-valvular leak, PVL) along the cuff causingvalve leakage and poor valve performance from regurgitation of bloodbetween the ventricle and the atrium and a lowering of blood pressure.These open areas may be round, oval or crescent shaped and must beclosed by surgical or other means. Today there is no ideal means ofclosing these valve leaks other than by surgery. Attempts have been madeby physicians to deploy devices as herein described by the Kotula el al'261 patent but this device has not been ideal for such variable sizedand shaped leaks. One of the most time consuming aspects of apercutaneous endoluminal approach to closing a PVL is locating theclosure device in the hole along the valve cuff.

Since the current devices are not steerable, it would be preferable thatthe device be delivered over a guidewire that can be more easilydirected across the leak prior to placing the device. An alternativeapproach would be placing the device through a steerable tip sheath.

Therefore, an additional need exists for a method for percutaneoustreatment of para-valvular leaks by use of an improved occlusion devicethat can be easily delivered over a guide wire or by a steerable sheath,in a low profile catheter based delivery system and which easilyaccommodates the variety of leak passageway shapes and sizes typical ofsuch valve leakage cases without interfering with valve leafletfunction.

The present invention provides a readily manufacturable solution to theaforementioned problems inherent in the prior art as represented by theKotula et al. '261 patent.

SUMMARY OF THE INVENTION

A collapsible medical device made in accordance with the presentinvention comprises multiple layers including an outer metal fabricsurrounding at least one, and possibly two or more, inner metalfabric(s) wherein each of the outer and inner metal fabrics eachcomprise a plurality of braided metal strands exhibiting an expandedpreset configuration. The collapsible medical device has proximal anddistal ends each incorporating clamps for securing the plurality ofbraided strands that comprise the inner and outer metal fabricstogether. It is to be understood that each of the several inner layersmay have their ends clamped individually and separately from the ends ofthe strands comprising the outer layer. The clamps for securing theplurality of metal strands may be oriented outward to form the deviceends or may alternatively be recessed inward from the functional ends ofthe device. The medical device is shaped to create an occlusion of anabnormal opening in a vascular organ when in its expanded presetconfiguration. The expanded preset configuration is deformable to alesser cross-sectional dimension for delivery through a channel in apatient's body. Both the outer and inner metal fabrics have a memoryproperty such that the medical device tends to return to the expandedpreset configuration when unconstrained. For example, by braiding theinner metal fabric(s) so as to have a greater number of braided metalstrands than are provided in the outer metal fabric and of a smallerwire diameter, the resulting device is still readily deformable to alesser cross-sectional dimension for delivery through a channel in apatient's body, yet the increase in the total number of metal strandscomprising the outer and inner metal fabrics result in a device thatprovides more immediate occlusion and does not require a sewn-inoccluding fabric. For example, the outer braided metal fabric may have,say, 72 strands; each of a first diameter while the inner metal fabricmay be braided from 144 strands, each of a smaller diameter than thediameter of the strands in the outer fabric layer. The outer metalfabric can also be braided from 144 or more strands.

In alternative embodiments the layers may be reversed in that theinnermost layer may have fewer braided wires of larger diameter than thelayers surrounding the inner layer. In another embodiment the layer withfewer wires of larger diameter may be between the inner and outermostlayer. In still another embodiment the layers may all have the samenumber of wires with the same or different wire diameters. In yetanother variation the layers may all have the same diameter of wireswith the same of different number of wires in each layer.

In other embodiments the various layers have different pre-set shapes inconcentric co-axial arrangement. In another embodiment the inner layersare side by side instead of coaxial with the outer layer. In stillanother embodiment an outer layer, that defines a pre-shaped butconformable volume, surrounds a concentric very much longer braid, preset into a bead & chain type shape. In this embodiment the internalbeaded chain braid is inserted into the outer braid volume to fill thevolume and cause the volume to take the shape of the cavity it is placedin. The filled volume results in quick hemostasis due to high metaldensity while maintaining a small diameter delivery profile.

BRIEF DESCRIPTION OF THE DRAWINGS

The foregoing features and advantages of the invention will becomeapparent to those skilled in the art from the following detaileddescription of a preferred embodiment, especially when considered inconjunction with the accompanying drawings in which like numerals in theseveral views refer to corresponding parts.

FIG. 1 is an enlarged, side elevation view of an ASD occluderincorporating the present invention;

FIG. 2 is an enlarged front elevation view of the device of FIG. 1;

FIG. 3 is an enlarged side elevation view of the device of FIG. 1 whenlongitudinally stretched;

FIG. 4 is a right end view of the device shown in FIG. 3;

FIG. 5 is an enlarged, side elevation view of a PDA occluderincorporating the present invention;

FIG. 6 is a right end view of the device of FIG. 5;

FIG. 7 is a greatly enlarged view like that of FIG. 6;

FIG. 8 shows a multi-layered vascular plug;

FIG. 9 shows the plug of FIG. 8 in combination with a center clamp;

FIG. 10 shows an alternative multi-layered vascular plug;

FIGS. 11a-11f are side and end views and cross-sectional views of analternative embodiment occluder for treatment of the PDA or VSD withviews of the occluder implanted in four varied anatomies;

FIGS. 12a-12f show variations of design incorporating different shapesfor each braid layer and means of connecting the layers & wire ends;

FIGS. 13a-13f are views of an example Para-Valvular Leak anatomy, andvarious optional occluder designs for treating PVL;

FIGS. 14a-14c are views of an embodiment having non coaxial innerbraids;

FIG. 15 is a drawing of an embodiment where by the inner braid fills theouter braid volume in serpentine fashion; and

FIGS. 16a-16d are views of an alternative embodiment for treatment ofpara-membranous ventricular septal defects (PMVSD).

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

The present invention provides a percutaneous catheter directedocclusion device for use in occluding an abnormal opening in a patients'body, such as an Atrial Septal Defect (ASD), a ventricular septal defect(VSD), a Patent Ductus arteriosus (PDA), a Patent Foramen Ovale (PFO),and the like. It may also be used in fabricating a flow restrictor or ananeurysm bridge or other types of occluders for placement in thevascular system. In forming a medical device, via the method of theinvention, a planar or tubular metal fabric is provided. The planar andtubular fabrics are formed of a plurality of wire strands having apredetermined relative orientation between the strands. The tubularfabric has metal strands which define two sets of essentially parallelgenerally helical strands, with the strands of one set having a “hand”,i.e. a direction of rotation, opposite that of the other set. Thistubular fabric is known in the fabric industry as a tubular braid.

The pitch of the wire strands (i.e. the angle defined between the turnsof the wire and the axis of the braid) and the pick of the fabric (i.e.number of wire cross-overs per inch) as well as some other factors, suchas the number of wires employed in a tubular braid and their diameter,are important in determining a number of properties of the device. Forexample, the greater the pick and pitch of the fabric, and hence thegreater the density of the wire strands in the fabric, the stiffer thedevice will be for a given wire diameter. Having a greater wire densitywill also provide the device with a greater wire surface area, whichwill generally enhance the tendency of the device to occlude a bloodvessel in which it is deployed. This thrombogenicity can be eitherenhanced by, e.g. a coating of a thrombolytic agent, or abated, e.g. bya coating of a lubricious, anti-thrombogenic compound. When using atubular braid to form a device of the Kotula '261 patent, a tubularbraid of about 4 mm in diameter with a pitch of about 50 degrees and apick of about 74 (per linear inch) would seem suitable for fabricatingdevices capable of occluding abnormal openings of about 2 mm to about 4mm in inner diameter. However, the occlusion may not be immediate.

A metal planar fabric is a more conventional fabric and may take theform of a flat woven sheet, knitted sheet or the like. In the wovenfabric there are typically two sets of metal strands, with one set ofstrands being oriented at an angle, e.g. generally perpendicular (havinga pitch of about 45 degrees), with respect to the other set. As notedabove, the pitch and pick of the fabric (or, in the case of a knitfabric, the pick and the pattern of the knit, e.g. Jersey or doubleknits) may be selected to optimize the desired properties of theresulting medical device.

The wire strands of the planar or tubular metal fabric are preferablymanufactured from so-called shape memory alloys. Such alloys tend tohave a temperature induced phase change which will cause the material tohave a preferred configuration which can be fixed by heating thematerial above a certain transition temperature to induce a change inthe phase of the material. When the alloy is cooled back down, the alloywill “remember” the shape it was in during the heat treatment and willtend to assume that configuration unless constrained from so doing.

Without any limitation intended, suitable wire strand materials may beselected from a group consisting of a cobalt-based low thermal expansionalloy referred to in the field as ELGELOY, nickel-based high temperaturehigh-strength “superalloys” commercially available from HaynesInternational under the trade name HASTELLOY, nickel-based heattreatable alloys sold under the name INCOLOY by International Nickel,and a number of different grades of stainless steel. The importantfactor in choosing a suitable material for the wire strands is that thewires retain a suitable amount of the deformation induced by a moldingsurface (as described below) when subjected to a predetermined heattreatment.

In the preferred embodiment, the wire strands are made from a shapememory alloy, NiTi (known as Nitinol) that is an approximatelystoichiometric alloy of nickel and titanium and may also include otherminor amounts of other metals to achieve desired properties. Handlingrequirements and variations of NiTi alloy composition are known in theart, and therefore such alloys need not be discussed in detail here.U.S. Pat. No. 5,067,489 (Lind) and U.S. Pat. No. 4,991,602 (Amplatz etal.), the teachings of which are incorporated herein by reference,discuss the use of shape memory NiTi alloys in guide wires. Such NiTialloys are preferred, at least in part, because they are commerciallyavailable and more is known about handling such alloys than other knownshape memory alloys. NiTi alloys are also very elastic and are said tobe “super elastic” or “pseudoelastic”. This elasticity allows a deviceof the invention to return to a preset expanded configuration followingdeployment.

When forming a medical device in accordance with the present invention,rather than having a single braided fabric layer, a plurality ofappropriately sized pieces of tubular or planar metal fabric areappropriately layered with respect to one another and inserted into thesame mold, whereby the fabric layers deform to generally conform to theshape of the cavities within the mold. The shape of the cavities is suchthat the plural metal fabric layers deform into substantially the shapeof the desired medical device. The ends of the wire strands of thetubular or planar metal fabric layers should be secured to prevent themetal fabrics from unraveling. A clamp or welding, as further describedbelow, may be used to secure the ends of the wire strands. Theadvantages of the present invention can also be achieved byheat-treating the inner and outer fabric layers separately and theninserting the inner layer or layers within the confines of the outerlayer.

It is further contemplated that the inner and outer fabric layers may beheat-set into different geometries and then assembled, one within theother, or may be heat set together in different geometries. In such casethe pitch of one braid may be selectively different from the other ifthe end wires of all layers are joined together at each end.Alternatively, the end wires of the multiple layers may be joinedtogether at only one end of the device and the other end may haveseparate layer end connectors where one end connector floats relative tothe other connector(s) at the same device end. This allows for the samepitch in all layers and accommodates the change in length that wouldoccur when two different shapes are compressed (axially elongated) fordelivery. It is also contemplated that one layer could be attached toanother layer, by for example a suture, at selective points in a middleportion of the device and not be co joined at the multiple layer braidwire ends. Where different layers have different shapes and havedifferent compressed axial lengths, the shorter axial length ends may beconnected to one or both ends of the longer length braid by an elasticmember(s). As will be further explained, FIGS. 12a-12f illustratesseveral examples of layers having different shapes and connections.

In the case of a tubular braid, a molding element may be positionedwithin the lumen of the braid prior to insertion into the mold tothereby further define the molding surface. If the ends of the tubularmetal fabric have already been fixed by a clamp or welding, the moldingelement may be inserted into the lumen by manually moving the wirestrands of the fabric layers apart and inserting the molding elementinto the lumen of the innermost tubular fabric. By using such a moldingelement, the dimensions and shape of the finished medical device can befairly accurately controlled and ensures that the fabric conforms to themold cavity.

The molding element may be formed of a material selected to allow themolding element to be destroyed or removed from the interior of themetal fabric. For example, the molding element may be formed of abrittle, frangible or friable material. Once the material has beenheat-treated in contact with the mold cavities and molding element, themolding element can be broken into smaller pieces, which can be readilyremoved from within the metal fabric. If this material is glass, forexample, the molding element and the metal fabric can be struck againsta hard surface, causing the glass to shatter. The glass shards can thenbe removed from the enclosure of the metal fabric.

Alternatively, the molding element can be formed of a material that canbe chemically dissolved, or otherwise broken down, by a chemical agentthat will not substantially adversely affect the properties of the metalwire strands. For example, the molding element can be formed of atemperature resistant plastic resin that is capable of being dissolvedwith a suitable organic solvent. In this instance, the fabric and themolding element can be subjected to a heat treatment to substantiallyset the shape of the fabric in conformance with the mold cavity andmolding element, whereupon the molding element and the metal fabric canbe immersed in the solvent. Once the molding element is substantiallydissolved, the metal fabric can be removed from the solvent.

Care should be taken to ensure that the materials selected to form themolding element are capable of withstanding the heat treatment withoutlosing their shape, at least until the shape of the multiple fabriclayers has been set. For example, the molding element could be formed ofa material having a melting point above the temperature necessary to setthe shape of the wire strands, but below the melting point of thestrands forming the metal fabric layers. The molding element and thelayers of metal fabric ultimately comprising the medical device can thenbe heat treated to set the shape of the metal fabric, whereupon thetemperature can be increased to substantially completely melt themolding element, thereby removing the molding element from within themetal fabric. Those skilled in the art will appreciate that the shapesof the mold cavities and the molding elements may be varied in order toproduce the medical device having a preselected size and shape.

It should be understood that the specific shape of a particular moldingelement produces a specific shape and other molding elements havingdifferent shape configurations may be used as desired. If a more complexshape is desired, the molding element and mold may have additional partsincluding a camming arrangement, but if a simpler shape is being formed,the mold may have few parts. The number of parts in a given mold and theshapes of those parts will be dictated almost entirely by the shape ofthe desired medical device to which the metal fabric will generallyconform.

When the multiple layers of tubular braid, for example, are in theirrelaxed configuration, the wire strands forming the tubular braids willhave a first predetermined relative orientation with respect to oneanother. As the tubular braids are compressed along their axis, thefabric layers will tend to flare out away from the axis conforming tothe shape of the mold. When so deformed, the relative orientation of thewire strands of the metal fabric layers will change. When the mold isassembled, the outer and inner metal fabrics will generally conform tothe molding surface of the cavity. The medical device has a presetexpanded configuration and a collapsed configuration which allows thedevice to be passed through a catheter or other similar delivery device.The shape of the fabric layers generally defines the expandedconfiguration when they are deformed to generally conform to the moldingsurface of the mold.

Once the tubular or planar metal fabric layers are properly positionedwithin a preselected mold with the metal fabric layers generallyconforming to the molding surface of the cavities therein, the fabriclayers can be subjected to a heat treatment while they remain in contactwith the molding surface. Heat-treating the metal fabric comprising theplural layers substantially sets the shapes of the wire strands fromwhich they are braided in a reoriented relative position when the fabriclayers conform to the molding surface. When the medical device isremoved from the mold, the fabric layers retain the shape of the moldingsurfaces of the mold cavities to thereby define a medical device havinga desired shape. This heat treatment will depend in large part upon thematerial of which the wire strands of the metal fabric layers areformed, but the time and temperature of the heat treatment should beselected to substantially set the fabric layers in their deformed state,i.e., wherein the wire strands are in their reoriented relativeconfiguration and the fabric layers generally conform to the moldingsurface.

After the heat treatment, the device is removed from contact with themold surfaces and will substantially retain its shape in a deformedstate. If a molding element is used, this molding element can be removedas described above.

The time and temperature of the heat treatment can very greatlydepending upon the material used in forming the wire strands. As notedabove, one preferred class of materials for forming the wire strands areshape memory alloys, with Nitinol, a nickel titanium alloy, beingparticularly preferred. If Nitinol is used in making the wire strands ofthe fabric layers, the wire strands will tend to be very elastic whenthe metal is in its austenitic phase; this very elastic phase isfrequently referred to as a super elastic or pseudo elastic phase. Byheating the Nitinol above a certain phase transition temperature, thecrystal structure of the Nitinol metal will tend to “set” the shape ofthe fabric layers and the relative configuration of the wire strands inthe positions in which they are held during the heat treatment.

Suitable heat treatments of Nitinol wire to set a desired shape are wellknown in the art. Spirally wound Nitinol coils, for example, are used ina number of medical devices, such as in forming the coils commonlycarried around distal links of guide wires and in forming other medicalproducts known in the art. A wide body of knowledge exists for formingNitinol in such devices, so there is no need to go into great detailhere on the parameters of a heat treatment for the Nitinol fabricpreferred for use in the present invention.

Briefly, though, it has been found that holding a Nitinol fabric atabout 500 degrees centigrade to about 550 degrees centigrade for aperiod of about 1 to 30 minutes, depending upon the size of the mold andthe stiffness of the device to be made will tend to set the fabriclayers in their deformed state, i.e., wherein they conform to themolding surface of the mold cavities. At lower temperatures, the heattreatment time will tend to be greater and at higher temperatures thetime will tend to be shorter. These parameters can be varied asnecessary to accommodate variations in the exact composition of theNitinol, prior heat treatment of the Nitinol, the desired properties ofthe Nitinol in the finished article, and other factors which will bewell known to those skilled in this field.

Instead of relying on convection heating or the like, it is also knownin the art to apply an electrical current to the Nitinol to heat it. Inthe present invention, this can be accomplished by, for example,connecting electrodes to opposed ends of the metal fabric layers.Resistance heating in order to achieve the desired heat treatment, whichwill tend to eliminate the need to heat the entire mold to the desiredheat-treating temperature, can then heat the wire. The materials,molding elements and methods of molding a medical device from a tubularor planar metal fabric is further described in U.S. Pat. Nos. 5,725,552,5,944,738 and 5,846,261 and assigned to the same assignee as the presentinvention, the entire disclosures of which are incorporated herein byreference.

Once a device having a preselected shape has been formed, the device maybe used to treat a physiological condition of a patient. A medicaldevice suitable for treating the condition, which may be substantiallyin accordance with one of the embodiments outlined below, is selected.Once the appropriate medical device is selected, a catheter or othersuitable delivery device may be positioned within a channel in apatient's body to place the distal end of the delivery device adjacentthe desired treatment site, such as immediately adjacent (or evenwithin) the shunt of an abnormal opening in the patient's organ forexample.

The delivery device (not shown) can take any suitable shape, butdesirably comprises an elongate flexible metal shaft or hypotube ormetal braided polymer tube having a threaded distal end for engagementwith a threaded bore formed in the clamp of the medical device. Thedelivery device can be used to urge the medical device through the lumenof a catheter/sheath for deployment in a channel of a patient's body.When the medical device is deployed out the distal end of the catheter,the delivery device still will retain it. Once the medical device isproperly positioned within the shunt of the abnormal opening, the shaftof the delivery device can be rotated about its axis to unscrew themedical device from the delivery means.

In one embodiment the occluder device, delivery catheter andcatheter/sheath accommodate a coaxial guidewire that slideably passesthrough the device, end clamps and delivery catheter central lumen, andtherefore helps guide the delivery device and outer catheter/sheath tothe desired location. The guidewire may be delivered independentlythrough the vasculature and across the targeted treatment location ormay be extended partially distal to the distal end of the deliverydevice and catheter/sheath and advanced with the delivery device andcatheter/sheath while the guidewire is manipulated to guide the occluderto the desired location. In another embodiment, the catheter/sheath issteerable to assist in placement of the delivery device and occluder.

By keeping the medical device attached to the delivery means, theoperator can retract the device for repositioning relative to theabnormal opening, if it is determined that the device is not properlypositioned within the shunt. A threaded clamp attached to the medicaldevice allows the operator to control the manner in which the medicaldevice is deployed out the distal end of the catheter. When the medicaldevice exits the catheter, it will tend to resiliently return to apreferred expanded shape, which is set when the fabric is heat-treated.When the device springs back into this shape, it may tend to act againstthe distal end of the catheter effectively urging itself forward beyondthe end of the catheter. This spring action could conceivably result inimproper positioning of the device if the location of the device withina channel is critical, such as where it is being positioned in a shuntbetween two vessels. Since the threaded clamp can enable the operator tomaintain a hold on the device during deployment, the spring action ofthe device can be controlled by the operator to ensure properpositioning during deployment.

The medical device can be collapsed into its reduced diameterconfiguration and inserted into the lumen of the catheter. The collapsedconfiguration of the device may be of any shape suitable for easypassage through the lumen of a catheter and proper deployment out thedistal end of the catheter. For example, an ASD occluding device mayhave a relatively elongated collapsed configuration wherein the devicesare stretched along their axes. This collapsed configuration can beachieved simply by stretching the device generally along its axis, e.g.by manually grasping the clamps and pulling them apart, which will tendto collapse the expanded diameter portions of the device inwardly towardthe device's axis. A PDA occlusion device also operates in much the samefashion and can be collapsed into its collapsed configuration forinsertion into the catheter by applying tension generally along the axisof the device. In this regard, these devices are not unlike “Chinesehandcuffs”, which tend to constrict in diameter under axial tension.

If the device is to be used to permanently occlude a channel in thepatient's body, one can simply retract the catheter and remove it fromthe patient's body. This will leave the medical device deployed in thepatient's vascular system so that it may occlude the blood vessel orother channel in the patient's body. In some circumstances, the medicaldevice may be attached to a delivery system in such a manner as tosecure the device to the end of the delivery means. Before removing thecatheter in such a system, it may be necessary to detach the medicaldevice from the delivery means before removing the catheter and thedelivery means.

Although the device will tend to resiliently return to its initialexpanded configuration, i.e., its shape prior to being collapsed forpassage through the catheter, it should be understood that it might notalways return entirely to that shape. For example, it may be desirablethat the device has a maximum outer diameter in its expandedconfiguration at least as large as and preferably larger than, the innerdiameter of the lumen of the abnormal opening in which it is to bedeployed. If such a device is deployed in a vessel or abnormal openinghaving a small lumen, engagement with the lumen will prevent the devicefrom completely returning to its expanded configuration. Nonetheless,the device would be properly deployed because it would engage the innerwall of the lumen to seat the device therein.

When the device is deployed in a patient, thrombi will tend to collecton the surface of the wires. By having a greater wire density andsmaller flow passages between wires as afforded by the multiple layerconstruction of the present invention, the total surface area of thewires and flow resistance will be increased, increasing the thromboticactivity of the device and permitting it to relatively rapidly occludethe vessel in which it is deployed. It is believed that forming theocclusion device with the outermost layer being 4 mm diameter tubularbraid whose strands are about 0.004 inch in diameter and having a pickof at least about 40 and a pitch of at least about 30 degrees andsurrounding an inner tubular braid whose strands are about 0.001 inchand of the same pick and pitch will provide sufficient surface area tosubstantially completely occlude an abnormal opening or blood vessel of2 mm to about 4 mm in inner diameter in a very short period of time ofless than five minutes. If it is desired to increase the rate at whichthe device occludes, a third or forth concentrically disposed braidedlayer can be added. Additionally the device wires may be coated with athrombogenic coating to aid in the occlusion rate.

Referring now to the drawings, a discussion of the embodiments of themedical device of the present invention will next be presented. FIGS.1-4 illustrate a first preferred embodiment of a medical device 10constructed in accordance with the present invention for correcting anatrial septal defect (ASD). With reference to FIGS. 1-4, the device 10is shown greatly enlarged so that the multiple layers comprising themedical device can be viewed. The ASD device is in its relaxed,non-stretched state with two aligned disks 12 and 14 linked together bya short middle cylindrical section 16 (FIG. 3). It is proposed that thisdevice 10 may also be well suited in occluding defects known in the artas patent foramen ovale (hereinafter PFO). Those skilled in the art willappreciate that a device of this configuration may also be suitable foruse in a transcatheter closure during a Fenestrated Fontan's procedure.ASD is a congenital abnormality of the atrial septum characterized bystructural deficiency of the atrial septum. A shunt may be present inthe atrial septum, allowing flow between the right and left atrialchambers of the heart. In large defects with significant left to rightshunts through the defect, the right atrium and right ventricle arevolume overloaded and the augmented volume is ejected into alow-resistance pulmonary vascular bed.

Pulmonary vascular occlusive disease and pulmonary atrial hypertensiondevelops in adulthood. Patients with secundum ASD with a significantshunt (defined as a pulmonary blood flow to systemic blood flow ratio ofgreater than 1.5) are operated upon ideally at two to five years of ageor whenever a diagnosis is made in later years. With the advent of twodimensional echocardiography and Doppler color flow mapping, the exactanatomy of the defect can be visualized. The size of the defect asdetermined by balloon measurement will correspond to the selected sizeof the ASD device 10 to be used.

The device 10, shown in its unconfined or relaxed state in FIGS. 1 and2, is adapted to be deployed within the shunt comprising an ASD or aPFO. For exemplary purposes, use of the device 10 in an ASD closureprocedure is described in the Kotula '261 patent referenced above andthose wishing further information are referred to that patent. Turningfirst to the constructional features of the device 10, the ASD occluderis sized in proportion to the shunt to be occluded. In the relaxedorientation, the metal fabric is shaped such that two disk like members12 and 14 are axially aligned and linked together by the shortcylindrical segment 16. The length of the cylindrical segment 16 whennot stretched preferably approximates the thickness of the atrialseptum, and ranges between 3 to 5 mm. The proximal disk 12 and distaldisk 14 preferably have an outer diameter sufficiently larger than theshunt to prevent dislodging of the device. The proximal disk 14 has arelatively flat configuration, whereas the distal disk 12 is preferablycupped towards the proximal end slightly overlapping the proximal disk14. In this manner, the spring action of the device 10 will cause theperimeter edge 18 of the distal disk to fully engage the sidewall of theseptum and likewise an outer edge of the proximal disk 14 will fullyengage an opposite sidewall of the septum. Perimeter edge 18 of disk 12as well as the perimeter edge of disk 14 may alternatively be configuredwith a larger radius outer edge compared to that shown in FIG. 1, todiminish forces on the tissue abutting the device.

In accordance with the present invention, the device 10 comprises anouter braided layer 20, a first inner layer 22 and possibly an optionalthird and innermost layer 24, thereby significantly increasing the wiredensity without unduly increasing the stiffness of the device or itsability to assume a decreased outer diameter upon longitudinalstretching. Multiple inner layers may be used as needed.

The ends of the tubular braided metal fabric device 10 are welded orclamped together with clamps as at 26, to avoid fraying. The ends of allof the layers may be grouped together and secured by two clamps, one ateach end or separate clamps can be applied on each end of the individuallayers. Of course the ends may alternately be held together by othermeans readily known to those skilled in the art. The clamp 26 tyingtogether the wire strands of the multiple layers at one end also servesto connect the device to a delivery system. In the embodiment shown inFIG. 1, the clamp 26 is generally cylindrical in shape and has a recess(not shown) for receiving the ends of the metal fabric to substantiallyprevent the wires comprising the woven fabric from moving relative toone another. The clamp 26 also has a threaded bore 28. The threaded boreis adapted to receive and engage a threaded distal end of a deliverydevice, such as a pusher wire.

The ASD occlusion device 10 of this embodiment of the invention canadvantageously be made in accordance with the method outlined above. Theouter layer 20 of device 10 is preferably made from a 0.004-0.008 inchdiameter Nitinol wire strands, but lesser or greater diameter strandscan be used as well. The braiding of the wire mesh comprising the outerlayer may be carried out with 28 picks per inch at a shield angle ofabout 64 degrees using a Maypole braider with 72 wire carriers. Thebraided layers 22 and 24 may each comprise 144 strands of Nitinol wireof a diameter in a range of from 0.001 inch to 0.002 inch, braided atthe same pitch. The stiffness of the ASD device 100 may be increased ordecreased by altering the wire size, the shield angle, the pick rate,and the number of wire carriers or the heat treatment process. Thoseskilled in the art will recognize from the preceding discussion that thecavities of a mold must be shaped consistent with the desired shape ofthe ASD device. Also, it will be recognized that certain desiredconfigurations may require that portions of the cavities be cammed. FIG.3 illustrates the ASD device 10 in a somewhat longitudinally stretchedstate. The distance separating the distal and proximal disks 12 and 14is preferably equal or slightly less than the length of the cylindricalsegment 16. The cup shape of each disk 12 and 14, ensures completecontact between the outer edge of each disk 12 and 14 and the atrialseptum. Upon proper placement, a new endocardial layer of endothelialcells forms over the occlusion device 10, thereby reducing the chance ofbacterial endocarditic and thromboembolisms.

The distance separating the disks 12 and 14 of occluding device 10 maybe increased to thereby provide an occluding device suitable for use inoccluding a channel within a patient's body, having particularadvantages in use as a vascular occlusion device. The device 10 includesa generally tubular middle portion 16 and a pair of expanded diameterportions 12 and 14. The expanded diameter portions are disposed ateither end of the generally tubular middle portion. The relative sizesof the tubular middle section 16 and the expanded diameter portions12-14 can be varied as desired. The medical device can be used as avascular occlusion device to substantially stop the flow of bloodthrough a patient's blood vessel. When the device 10 is deployed withina patient's blood vessel, it is positioned within the vessel such thatits longitudinal axis generally coincides with the axis of the vesselsegment in which it is being inserted. The dumbbell shape is intended tolimit the ability of the vascular occlusion device to turn at an anglewith respect to the axis of the blood vessel to ensure that it remainsin substantially the same position in which the operator deploys itwithin the vessel.

In order to relatively strongly engage the lumen of the blood vessel,the maximum diameter of the expanded diameter portions 12-14 should beselected so that it is at least as great as the diameter of the lumen ofthe vessel in which it is to be deployed and is optimally slightlygreater than that diameter. When it is deployed within the patient'svessel, the vascular occlusion device will engage the lumen at twospaced apart locations. The device is desirably longer along its axisthan the dimensions of its greatest diameter. This will substantiallyprevent the vascular occlusion device 10 from turning within the lumenat an angle to its axis, essentially preventing the device from becomingdislodged and tumbling along the vessel within the blood flowing throughthe vessel.

The relative sizes of the generally tubular middle portion 16 andexpanded diameter portions 12-14 of the vascular occlusion device can bevaried as desired for any particular application by appropriateselection of a mold to be used during the heat setting of the device.For example, the outer diameter of the middle portion 16 may rangebetween about 1/4 and about 1/3 of the maximum diameter of the expandeddiameter portions and the length of the middle portion 16 may compriseabout 20% to about 50% of the overall length of the device 10. Althoughthese dimensions are suitable if the device is to be used solely foroccluding a vascular vessel, it is to be understood that thesedimensions may be varied if the device is to be used in otherapplications, such as a ventricular septal defect occluder (VSD).

The aspect ratio (i.e., the ratio of the length of the device over itsmaximum diameter or width) of the device 10 illustrated in thisembodiment is desirably at least about 1.0, with a range of about 1.0 toabout 3.0 being preferred and then aspect ratio of about 2.0 beingparticularly preferred. Having a greater aspect ratio will tend toprevent the device 10 from rotating generally perpendicularly to itsaxis, which may be referred to as an end-over-end roll. So long as theouter diameter of the expanded diameter portions 12-14 of the device 10is large enough to seat the device fairly securely against the lumen ofthe channel in which the device is deployed, the inability of the deviceto turn end-over-end will help keep the device deployed precisely whereit is positioned within the patient's vascular system or in any otherchannel in the patient's body. Alternatively, having expanded diameterportions 12-14 which have natural relaxed diameters substantially largerthan a lumen of the vessels in which the device is deployed should alsosuffice to wedge the device into place in the vessel without undueconcern being placed on the aspect ratio of the device.

Referring next to FIGS. 5-7, there is shown generally a device 100suitable for occluding a patent ductus arteriosus (PDA). PDA isessentially a condition wherein two blood vessels, the aorta and thepulmonary artery adjacent the heart, have a shunt between theirrespective lumens. Blood can flow directly between these two bloodvessels through the shunt, resulting in cardiac failure and pulmonaryvascular disease. The PDA device 100 has a generally bell-shaped body102 and an outwardly flaring forward end 104. The bell-shaped body 102is adapted to be positioned within the aorta to help seat the body ofthe device in the shunt. The sizes of the body 102 and the end portion104 can be varied as desired during manufacture to accommodate differentsized shunts. For example, the body 102 may have a diameter along itsgenerally slender middle of about 10 mm and a length along its axis ofabout 25 mm. In such a medical device 100, the base of the body mayflare generally radially outward until it reaches an outer diameterequal to that of the forward end 104 which may be on the order of about20 mm in diameter.

The base 106 desirably flares out relatively rapidly to define ashoulder 108, tapering radially outwardly from the body 102. When thedevice 100 is deployed in a vessel, this shoulder 108 will abut theperimeter of the lumen being treated with higher pressure. The forwardend 104 is retained within the vessel and urges the base of the body 102open to ensure that the shoulder 108 engages the wall of the vessel toprevent the device from becoming dislodged from within the shunt.

A PDA occlusion device 100 of this embodiment of the invention canadvantageously be made in accordance with the method outlined above,namely deforming multiple layers 110, 112 and 114 (FIG. 7) of generallyconcentrically oriented tubular metal fabric to conform to a moldingsurface of a mold and heat-treating the fabric layers to substantiallyset the fabric layers in their deformed state. With continued referenceto the greatly enlarged view of FIG. 7, the outer layer 110 comprises aframe that defines the outer shape of the medical device 100. It ispreferably formed from 72 or 144 braided strands whose diameters are ina range of from 0.003 to about 0.008 inch. The pitch of the braid may bevariable. Within this frame is the layer 112 that forms an outer liner.It may also prove expedient to incorporate a third layer 114 as an innerliner. The outer and inner liners may be braided using 144 strands of ashape memory wire whose diameter may be 0.001 to 0.002 inch. The pitchof the braid in layers 112 and 114 should be the same. As noted above,the ends 116 and 118 of the braided layers should be secured in order toprevent the braids from unraveling. In the preferred embodiment, clamps120 are used to tie together the respective ends of the wire strands oneach end 116 and 118 of the tubular braid members forming the occlusiondevice 100. Alternatively, different clamps may be used to secure theends of the metal strands of the outer fabric layer than are used tosecure the ends of the metal strands of each of the inner layers. It isto be understood that other suitable fastening means may be attached tothe ends in other ways, such as by welding, soldering, brazing, use ofbiocompatible cementious material or in any other suitable fashion. Oneor both clamps 120 of the outer layer may include a threaded bore 122that serves to connect the device 100 to a delivery system (not shown).In the embodiment shown, the clamps 120 are generally cylindrical inshape and have a crimping recess for receiving the ends of the wirestrands to substantially prevent the wires from moving relative to oneanother.

When using untreated NiTi fabrics, the strands will tend to return totheir unbraided configuration and the braided layers 110, 112 and 114can unravel fairly quickly unless the ends of the length of the braidedlayers that are cut to form the device are constrained relative to oneanother. The clamps 120 are useful to prevent the layers of braid fromunraveling at either end. Although soldering and brazing of NiTi alloyshas proven to be fairly difficult, the ends can be welded together, suchas by spot welding with a laser welder. When cutting the fabriccomprising the multiple layers 110, 112 and 114 to the desireddimensions, care should be taken to ensure that the fabric layers do notunravel. In the case of tubular braids formed of NiTi alloys, forexample, the individual strands will tend to return to their heat setconfiguration unless constrained. If the braid is heat treated to setthe strands in the braided configuration, they will tend to remain inthe braided form and only the ends will become frayed. However, it maybe more economical to simply form the braid without heat-treating thebraid since the fabric will be heat treated again in forming the medicaldevice.

Once the fabric is compressed so as to conform to the walls defining themold interior, the fabric layers can be subjected to a heat treatmentsuch as is outlined above. When the mold is open again the fabric willgenerally retain its deformed, compressed configuration. The formeddevice 100 can be collapsed, such as by urging the clamps 120 generallyaxially away from one another, which will tend to collapse the device100 toward its axis. The collapsed device can then be attached to adelivery device, such as an elongated flexible push wire and passedthrough a delivery catheter for deployment in a preselected site in thepatient's body. The use of the resulting device to occlude a PDA is thesame as has been described in the Kotula '261 patent and need not berepeated here.

Because of the significant increase in the number of wire strands in thecomposite multi-layer structure, it is no longer necessary toincorporate a sewn-in polyester material in order to reduce the timerequired to establish total occlusion of a PDA. This not only reducesthe cost of manufacture but also facilitates loading of the resultingdevice into a delivery catheter of a reduced French size. Reduced Frenchsize means ability to treat smaller patents which is a major advantage.

FIGS. 8-10 show various vascular plug arrangements. These plugs areideally suited for treating a variety of arterial-venous malformationsand aneurysms. These plugs can also be used to block blood flow to atumor or lesion. Likewise, these plugs can be used to bloc fluid flowthrough a portion of the vasculature of the body in connection with thetreatment of other medical conditions.

Each embodiment shown in FIGS. 8-10 has a multi-layered braidedstructure 150, i.e., two or more layers of braided fabric. When themulti-layered braided structure has a tubular shape, a pair of endclamps 152 and 154 are provided to prevent the multi-layered braidedstructure from unraveling. Those skilled in the art will recognize thatonly a single end clamp is required if the braids are in the form of asack as opposed to having a tubular shape.

The embodiment shown in FIG. 8 has a cylindrical wall 155 with two faces156 and 158 at the opposite ends. Generally speaking, when the device isin its expanded configuration as shown in FIG. 8, the cylindrical wallabuts the wall of the vessel in which the device is deployed to hold thedevice in place. The two faces 156 and 158 preclude fluid flow past thedevice.

In some treatment situations, it may be desirable to increase the numberof faces to increase the ability of the device to block fluid flow pastthe device. FIGS. 9 and 10 show how this can be accomplished.

The device shown in FIG. 9 also has a cylindrical wall 155, a proximalface 156 and a distal face 158. The embodiment of FIG. 9 furtherprovides an intermediate clamp 160 clamping an intermediate portion ofthe multi-braided material. This divides the cylindrical wall into twosections 155 a and 155 b and forming two additional faces 162 and 164.When the device of FIG. 9 is deployed, the two sections 155 a and 155 bof cylindrical wall 155 still abuts the vessel wall to hold the devicein place yet fluid must to traverse all for faces (namely faces 156,158, 162 and 164) to flow past the device. The reduction in flowprovided by the two additional faces 162 and 164 can result in fasterclotting.

FIG. 10 shows the same basic structure as FIG. 9. The primary differenceis that the application of the intermediate clamp 160 results in the twosections 155 a and 155 b having a bulbous rather than a cylindricalform. The widest part of sections 155 a and 155 b still engage thevessel wall and hold the device in place after deployment. There arealso still four faces (156, 158, 162 and 164) even though they arecurved as opposed to flat as shown in FIG. 9.

The intermediate clamp 160 can be made of any suitable material. Suturethread has proven to be effective. The two end clamps 152 and 154 arepreferably made of a radiopaque material so they can easily bevisualized using, for example, a fluoroscope. The intermediate clamp canbe made of such material as well. Also, additional intermediate clampscan be added to further increase the number of faces. For example, iftwo intermediate clamps are used, a total of six faces would be present.With each additional clamp, two additional faces are provided.

Also, when the multi-layered braided structure (or at least one of thelayers thereof) is made of a super elastic or shape memory material, itmay be possible to eliminate the intermediate clamps and instead moldthe device to have such a shape (e.g., a shape such as that shown inFIG. 8) when fully deployed and in its expanded preset configuration. Ofcourse, all such embodiments, including those shown in FIGS. 8-10, aredeformable to a lesser cross-sectional dimension for delivery through acatheter.

An alternative improved embodiment for the treatment of Patent DuctusArteriosus (PDA) is shown is FIGS. 11a-11d . The following dimensionsare given in relation to the typical size range for PDA pediatricpassageways and not intended as a limitation. The PDA occlusion device200 of this embodiment of the invention can advantageously be made inaccordance with the method outlined above, namely deforming multiplelayers 210, and 212 of generally concentrically oriented tubular metalfabric to conform to a molding surface of a mold and heat-treating thefabric layers to substantially set the fabric layers in their deformedstate. The at least two layers of braid in this device have the samemolded shape. The occlusion device 200 has two disks 202, 204, one ateach end that has an outer portion, starting at diameter C and extendingto diameter B, tapered toward the device center at an angle F thatranges from 20 to 40 degrees, preferably 30 degrees. Each disk has acentral portion 206 that is perpendicular to the device 200 central axisand extends outward to a diameter C that ranges from 3 mm to 6 mm. Eachdisk is a mirror image of the other disk with an outer diameter B thatranges from 9 mm to 12 mm. The disks are thin with the disk wallessentially little more than the thickness of the 2 layers formed backto back, ranging from 0.005 to 0.010 inch, preferably 0.007 inch or adouble wall thickness (4 layers) of 0.014 inch.

The device 200 includes a central cylindrical portion 214 of diameter Cwhich ranges from 2 mm to 6 mm. The length of the cylindrical centralsection A, ranges from 2 mm to 8 mm. Between the disks at each end andthe central cylindrical portion is a very reduced diameter E whichranges from 1 mm to 2 mm, preferably 1 mm (or a tightly bunched group ofwires). The ratio of the large disk diameter B to the small diameter Eranges from 6 to 12.

This high ratio provides the ability of the disks to conform (pivot) toa wide range of wall angles relative to the axis of the PDA. Thisconformability is shown in four examples in FIG. 11c-11f . FIG. 11cillustrates a condition where the disks 202, 204 are relatively parallelbut at a substantial angle to the central section or device axis. Thecentral section is elongated due to a smaller passage than anticipatedand the elongation accommodates the lengthen passage between disks. InFIG. 11d the disks are non-parallel to accommodate the walls of theaorta and again the central section is elongated as it conforms to thepassageway between the disks. FIG. 11e illustrates a device placed in apara-membranous VSD. In this case the device is shown conforming to athin membrane at the upper portion of the defect and to the thickerseptum in the bottom portion of the defect. The central section fullyexpands to shorten the distance between disks to aid in clamping forceand to fill the defect. FIG. 11f shows a device placed in a tear througha ventricular septum. The device central section 214 elongates to fillthe tear and the disks conform to the septum walls.

The ratio of diameters B to E and C to E, as defined in FIG. 11a ,allows both the disks and central cylindrical portion to articulateabout diameter E at an angle to the device axis and to conform moreeasily to vessel passageway variability and tissue irregularity at thedisk contact area. Diameter C is selected to be a little larger (10-20%)than the passageway it is intended for, to provide some anchoring of thedevice. If the passageway is longer than anticipated the central portioncan elongate to accommodate the longer length. The disks are spacedapart at there outermost point a distance D that ranges from 1 mm to 3mm, preferably 1 mm. The distance between the inner surface of eachdisk, in the portion (C) perpendicular to the device central axis, is Gand ranges from 3 to 7 mm, preferably 5 mm. The difference betweendistance G and A provides for passageway length variability andconformability to surface irregularities as well as acts like a springto apply clamping pressure at each disk to the vessel to hold the devicein place.

With continued reference to the greatly enlarged view of FIG. 11a , theouter layer 210 comprises a frame that defines the outer shape of themedical device 200. It is preferably formed from 72 braided strandswhose diameters are in a range of from 0.001 to about 0.005 inch,preferably 0.0015 in. The pitch of the braid ranges from 45 to 70degrees, preferably 60 degrees. Within this frame is the inner layer 212having the same shape as outer layer 210. The inner layer is preferablybraided using 144 strands of a shape memory wire whose diameter may be0.001 to 0.003 in., preferably 0.0015 in. The pitch of the braid inlayers 210 and 212 are preferably the same but can also be differentwithout departing from the scope of the invention. As noted above, theends 216 and 218 of the braided layers should be secured in order toprevent the braids from unraveling. In the preferred embodiment, clamps220, made from platinum-iridium or stainless steel, are used to tietogether the respective ends of the wire strands on each end 216 and 218of the tubular braid members forming the occlusion device 200. Theclamps 220 are preferably oriented outward from the disks as shown inFIG. 11a but may alternatively be recessed within the disk surfacesomewhat, although full recess of the clamps would require a recess inthe central portion end walls and the disk walls to accommodate theclamp length. Alternatively, different clamps may be used to secure theends of the metal strands of the outer fabric layer than are used tosecure the ends of the metal strands of each of the inner layers. It isto be understood that other suitable fastening means may be attached tothe ends in other ways, such as by welding, soldering, brazing, use ofbiocompatible cementious material or in any other suitable fashion. Oneor both clamps 220 may include a threaded bore 222 that serves toconnect the device 200 to a delivery system (not shown). In theembodiment shown, the clamps 220 are generally cylindrical in shape andhave a crimping recess for receiving the ends of the wire strands tosubstantially prevent the wires from moving relative to one another.

When using untreated NiTi fabrics, the strands will tend to return totheir unbraided configuration and the braided layers 210, and 212 canunravel fairly quickly unless the ends of the length of the braidedlayers that are cut to form the device are constrained relative to oneanother. The clamps 220 are useful to prevent the layers of braid fromunraveling at either end. Although soldering and brazing of NiTi alloyshas proven to be fairly difficult, the ends can be welded together, suchas by spot welding with a laser welder. When cutting the fabriccomprising the multiple layers 210, and 212 to the desired dimensions,care should be taken to ensure that the fabric layers do not unravel. Inthe case of tubular braids formed of NiTi alloys, for example, theindividual strands will tend to return to their heat set configurationunless constrained. If the braid is heat treated to set the strands inthe braided configuration, they will tend to remain in the braided formand only the ends will become frayed. However, it may be more economicalto simply form the braid without heat-treating the braid since thefabric will be heat treated again in forming the medical device.

In one embodiment of the occluder (not shown) designed to be advancedover a guidewire, the clamps 220 may comprise two concentric rings withthe braid wires constrained between the rings, by either using theprevious described methods or by swaging the outer ring against thewires and the inner ring. The use of an inner ring in the clamps 220,provides a central lumen for slidable passage of the guidewire. Thetreaded clamp can either use internal threads (inner ring) or externalthreads (outer ring), provided that a passage for the guidewire ispresent.

Once the fabric is compressed so as to conform to the walls defining themold interior, the fabric layers can be subjected to a heat treatmentsuch as is outlined above. When the mold is open again the fabric willgenerally retain its deformed, compressed configuration. The formeddevice 200 can be collapsed, such as by urging the clamps 220 generallyaxially away from one another, which will tend to collapse the device200 toward its axis. The collapsed device can then be attached to adelivery device, such as an elongated flexible push wire and passedthrough a delivery catheter for deployment in a preselected site in thepatient's body. The use of the resulting device to occlude a PDA is thesame as has been described in the Kotula '261 patent and need not berepeated here.

Other alternative embodiments are shown diagrammatically in FIGS.12a-12f . Each of the designs incorporate the beneficial features, rangeof dimensions, fabric selection, etc., of the prior embodiments exceptas noted. In FIG. 12a the disks 202′ and 204′ are fabricated from asingle layer folded back on itself, while the central portion is doublelayered. In this case the pitch of the inner layer would have to beincreased relative to the outer layer so that both layers had the samecollapsed length. This gives flexibility to the designer to havedifferent characteristics in the disk portion relative to the centralportion of the device. FIG. 12f shows an embodiment where the design isreversed to have double layers in the disk portion back to back, with asingle layer in the central portion or a different shape for each layerin the central portion as shown.

FIG. 12b illustrates a design variation where the multiple braid layershave end wires connected at one end in a common clamp but where theinner layer at the opposite end has a clamp that free floats and isseparate from the clamp for the outer layer. In this design there isfreedom to have different compressed braid lengths so that the pitch maybe varied as desired. The inner layer could also follow the shape of theouter layer in entirety if desired with a different pitch betweenlayers.

In the embodiment of FIG. 12c the inner layer 212 is suspended by sutureconnectors between the layers and the end clamps of each layer areindependent of each other.

In FIG. 12d the inner layer 212 has independent end clamps as in FIG.12c , but rather than the layers connected by sutures, the layers 210and 212 have their end clamps connected by elastic members, such as madefrom silicone rubber. FIG. 12e is similar to FIG. 12d except that theconnector could be a non-elastomer such as suture or wire and may beconnected optionally at only one set of end clamps. All embodimentsshown in FIGS. 12a-12f have a relatively small diameter E in comparisonto diameters B and C to maintain the articulation benefits. Diameters A,B, C and E are defined as in FIG. 11a . It is anticipated that thevarious optional characteristics, as shown in FIGS. 12a-12f , could becombined in any manner desired for any embodiment described herein.

Various embodiments for treating Para-Valvular Leaks (PVL) areillustrated in FIGS. 13a-13f . FIG. 13a shows an artificial bi-leafletvalve sewn by suture 232 into a patient. Three cross-hatched areas 234,236 and 238 along the valve cuff represent open areas where tissue haspulled away from the cuff from weak tissue or broken or loose sutures.These open areas allow blood to short circuit the valve and result inpoor heart function and lower blood pressure. The invention herein isdesigned to close/occlude these PVLs such as are shown in FIGS. 13a -13f.

A PVL occlusion device 300 of this embodiment of the invention canadvantageously be made in accordance with the method outlined above,namely deforming multiple layers 310, 312 of generally concentricallyoriented tubular metal fabric to conform to a molding surface of a moldand heat-treating the fabric layers to substantially set the fabriclayers in their deformed state. With continued reference to the greatlyenlarged view of FIG. 13b -I, the outer layer 310 comprises a frame thatdefines the outer shape of the medical device 300. It is preferablyformed from 144 braided strands whose diameters are in a range of from0.0015 to about 0.0035 inch preferably 0.002 inch. The pitch of thebraid may range from 45 to 70 degrees, preferably 60 degrees. Withinthis frame is the inner layer 312. It may also prove expedient toincorporate a third layer 314 (not shown) as an innermost liner. Theinner layer may be braided using 144 strands of a shape memory wirewhose diameter ranges from 0.001 to 0.002 inch, preferably 0.0015 inch.The pitch of the braid in layers 310 and 312 preferably are the same. Asnoted above, the ends 316 and 318 of the braided layers should besecured in order to prevent the braids from unraveling. In the preferredembodiment, clamps 320 are used to tie together the respective ends ofthe wire strands on each end 316 and 318 of the tubular braid membersforming the occlusion device 300. Alternatively, different clamps may beused to secure the ends of the metal strands of the outer fabric layerthan are used to secure the ends of the metal strands of each of theinner layers. It is to be understood that other suitable fastening meansmay be attached to the ends in other ways, such as by welding,soldering, brazing, use of biocompatible cementious material or in anyother suitable fashion. One or both clamps 320 of the outer layer mayinclude a threaded bore 322 that serves to connect the device 300 to adelivery system (not shown). In the embodiment shown, the clamps 320 aregenerally cylindrical in shape and have a crimping recess for receivingthe ends of the wire strands to substantially prevent the wires frommoving relative to one another.

When using untreated NiTi fabrics, the strands will tend to return totheir unbraided configuration and the braided layers 310, and 312 canunravel fairly quickly unless the ends of the length of the braidedlayers that are cut to form the device are constrained relative to oneanother. The clamps 320 are useful to prevent the layers of braid fromunraveling at either end. Although soldering and brazing of NiTi alloyshas proven to be fairly difficult, the ends can be welded together, suchas by spot welding with a laser welder. When cutting the fabriccomprising the multiple layers 310, and 312 to the desired dimensions,care should be taken to ensure that the fabric layers do not unravel. Inthe case of tubular braids formed of NiTi alloys, for example, theindividual strands will tend to return to their heat set configurationunless constrained. If the braid is heat treated to set the strands inthe braided configuration, they will tend to remain in the braided formand only the ends will become frayed. However, it may be more economicalto simply form the braid without heat-treating the braid since thefabric will be heat treated again in forming the medical device.

Since the PVL openings are of various shapes it is anticipated that anumber of sizes and shapes of occluder devices may be needed to closethese leaks. It is also important that the occluder be positionedsecurely to prevent migration or embolization of the device. As shown inFIG. 13b -I, device 300 is formed of two layers each having the sameshape. FIG. 13b -II is a plan view of device 300 and FIG. 13b -III is anend view thereof. This particular design is intended to occlude openingsthat are somewhat oblong in shape. Radiopaque markers 330 may be placedeither on the narrow or wide side of the expanded shape to help thephysician orient the device as needed. These markers may be radiopaqueplatinum wire or platinum iridium markers attached to the braid inmanner which does not impede braid collapse or self expansion. Since thewire diameter is small, the oblong shape can conform to shapes that maybe more rounded or longer. FIG. 13c illustrates a crescent shapedoccluder 324 and FIG. 13d illustrates a round occluder 326. In FIG. 13e, one edge of the device that interfaces with the cuff 240 is shaped tomatch the cuff shape whereas the other side that interfaces with thetissue 242 has a shape more conducive to the thickness of the tissue atthe interface. For illustrative purposes, dimensions are given for theoblong occluder of FIG. 13b but are similar for other shapes whereapplicable. All dimensions are in mm.

A=6, B=2, C=10, D=6, E=6, F=9, G=7, H=2

In FIG. 13f is shown a preferred clamp 320 for the device 300 intendedto be compatible with delivery of the occluder over a guidewire. In thisdesign the clamps 320 must have a central passage 328 for the guidewireto slidable pass there through. The clamp 320 is therefore fabricatedwith an inner ring 330 having an inside diameter slightly larger (about0.002-0.004 inch) larger than the guidewire diameter. The clamp also hasan outer ring 332 large enough to contain the braided wire ends betweenthe two rings. The outer ring may be swaged to compress the outer ringagainst the wires and the inner ring or the wire ends and rings may bewelded, brazed, soldered or held by adhesive or other known means. Atleast one of the clamps has threads either external on the outer ring ofthe clamp or internally in the inner ring. If internal threads are usedthe inner ring must be enlarged to accommodate a male threaded deliverydevice with an internal lumen sized for passage of a guide wire throughthe threaded clamp.

An over the guidewire delivery system is particularly useful in deliveryof an occluder for PVL cases. One of the most difficult aspects of thecase is delivering the device through the defect near the valve cuff.Due to the turbulence of blood in the area of the valve it is preferableto place a small surface area steerable guidewire through the defectfirst and then advance the delivery device and catheter over theguidewire. Alternatively the guidewire may be placed through thecatheter and delivery device and lead the passage of the system throughthe vasculature. Near the valve defect the guidewire may beindependently maneuvered through the defect and then the catheter anddelivery device may be advanced over the guidewire.

A method of treating a pera-valular leak may involve the followingsteps: (1) advance a guidewire through the vasculature of the body andacross the pera-valular leak opening; (2) advance over the guidewire acatheter containing a occluder connected to a delivery device until thedistal tip of the catheter crosses the pera valular leak opening; (3)deploy the distal portion (distal to waist) of the occluder bymanipulating the deliver device to extend the distal portion of theoccluder beyond the distal end of the catheter causing the distalportion to self expand toward it's preset shape; (4) pulling proximallythe catheter and delivery device until the expanded portion of theoccluder contacts tissue adjacent one side of the opening; (5)withdrawing the catheter proximally relative to the delivery device, toexpose the remaining proximal portion of the occluder while allowing thedeliver device to advance distally as the occluder self expands andcontacts tissue adjacent the opposite side of the opening; (6)disconnecting the delivery device from the occluder once the device isplaced properly to occlude the opening; and (7) removing the deliverydevice and catheter from the body.

An alternative method of treating a pera-valvular leak is similar toabove but includes the step of: advancing the guidewire through thevasculature through a preshaped or steerable catheter to facilitatepassage through the peri-valvular leak opening. An optional additionalstep includes: removing the catheter after crossing the leak opening andbefore delivery of the occluder.

Another embodiment of an occluder is a variation of the devices shown inFIGS. 12a-12f , whereby the occluder device 400, as shown in FIGS.14a-14c , consists of a soft, conformable, outer braid 410 enclosing avolume 430 that is pre-shaped as desired, with two or more internalbraided tubular members 412 a, b, c side by side with shared braid endwire connectors at least at one end. As can be seen in FIGS. 14b and 14c, the multiple braids need not be concentric. This arrangement allowsthe inner braided members 412 to shift relative to one another to fillthe available volume of unknown size or shape such as an oblong,crescent, or oval cavity shape. This is accomplished by selecting a heatset shape for braids 412 that have a large enough diameter to exertforce against the outer tubular braid to compel the outer braid againstthe wall of the cavity the device is placed in. To share a common endwire clamp the internal tubular braid walls must be compressed againsteach other at the ends and shaped into a crescent to fit in annularfashion about a wire end clamp as shown at clamp 420 of FIG. 14a . Theproximal clamp 420 at wire end 418 contains threads (not shown) forconnection to the delivery catheter, not shown. The proximal clamp 420may or may not also clamp the ends of the inner braid proximal wireends. It is preferable that the proximal wire ends of braids 412 beconnected to clamp 420 by means of a tether or elastic member to allowfor a braid length change that would vary based on the shape of thedevice 400 within a cavity. The outer braid for this embodiment could bea braid of 144 Nitinol wires of a diameter of between 0.001-0.002inches. The inner braids may be fashioned from either 72 or 36. Nitinolwires with a diameter of 0.001-0.003 inches. An optional over theguidewire delivery embodiment is practical by using wire end clamps 420that are of the two ring design as described in previous embodiments.

In a further embodiment 500 as shown in FIG. 15 the outer braid 510 ispre-shaped to define a particular volume shape 530. Contained within theouter braid and coaxially sharing the outer braid distal wire end clamp520 is a smaller diameter tubular braid 512 that is pre-shaped into abead and chain shape. The internal smaller braid 512 is much longer thanthe outer braid 510 and is designed to meander into the outer braiddefined volume 530 as braid 512 is inserted to fill the volumecompletely and help the outer braid to conform to the cavity shape it iswithin. The distal braided wire end clamp 520 at wire end 516 ispreferably a two part clamp arrangement with an internal ring andexternal ring pinching the braid wires between the rings. The proximalbraided wire end clamp 522 is similarly constructed but the outer ringis threaded to mate with threads on the delivery catheter 540 forselective connection between the device and the delivery catheter. Inthis embodiment a portion of the inner braid remains within the deliverycatheter when the outer braid is fully deployed. In order to deliver thebalance of the inner tubular braid 512 into the volume 530, a pusherwire 528 within the delivery catheter 540 acts against the proximal endwire end clamp 523 of braid 512 to advance the braid completely out ofthe delivery catheter. The pusher wire 528 may optionally have athreaded end to engage with optional threads in the wire end clamp 523.The delivery catheter 540 would be advanced to the treatment sitethrough a sheath. The high density of wire within the volume 530 aids inrapid hemostasis while maintaining a low profile for delivery. Thespherical shape of the bead chain fills the volume with sphere againstsphere against the outer braid and thereby loads the outer braid surfaceagainst the cavity wall desired to be occluded. For this embodiment, theouter braid should be soft and conformable. A braid of 144 Nitinol wiresof 0.001-0.002 inch diameter should be suitable. The inner braid may beeither 72 or 36 Nitinol wires and the wire diameter may be between 0.001to 0.003 inch. The outer and inner braided layers are heat set aspreviously described in the desired volume shape and beaded chain shapeas desired. The wire end clamps 520 and 523 may be of the two ringconfiguration as previously described in other embodiments to allow thedevice to be configured for over the guidewire delivery.

A method of occluding a body cavity consists of the following steps: (1)providing an occluder comprising at least a first self expanding braidedtubular layer defining a preset volume shape and a second braided memberlonger than the first braided member in the collapsed for deliveryconfiguration, the second braided member coaxially connected at one endto the end of the first braided layer, the second braided member havinga repeating preset volume occupying shape much smaller than the presetshape of the first braided layer, whereby both first and second braidedmembers have a collapsed elongated low profile shape for deliverythrough a catheter and a self expanding preset volume occupying spacefor occlusion of a body cavity; (2) advancing the distal tip of adelivery catheter containing the occluder and a delivery device to abody cavity; (3) advancing the distal end of the occluder out of thecatheter to allow the occluder first braided layer to self expand withinthe cavity; advancing the second braided member distally within thevolume occupied by the first braided layer until the entire selfexpanded second braided member is contained within the volume; (4)disconnecting the delivery device from the occluder; (5) removing thecatheter and delivery device from the body. An optional additional stepto the above method is to deliver the occluder, delivery device andcatheter over a guidewire and removal of the guidewire from the cavity,prior to self expansion of the first braided layer.

In another embodiment as shown in FIGS. 16a-16d , intended primarily forpara-membranous VSD occlusion, the device central diameter is relievedwith a flattened or inverted portion in the circumference to relievepressure on the heart's conductive His bundle at the muscular portion ofthe septum, to prevent heart block (FIG. 16a ). Additionally, the devicehas only one articulating flange 600 (right chamber) with a smalldiameter E and the flange 602 on the opposing end (left chamber) isrelieved in diameter to prevent interference with the aortic valve. Itis anticipated that the single articulating flange 600 will reducepressure of the conductive His bundle to help prevent heart block andthat the lack of articulation on the left chamber side will betterresist dislodgement of the device from the higher arterial bloodpressure (FIGS. 16b and 16c ). An alternative embodiment for relievingthe left chamber flange 602 diameter to prevent interference with theaortic valve is to move the left chamber flange off axis to the centraldevice portion so the flange is displaced away from the valve as shownin FIG. 16d . Further modification, by eliminating both flangearticulations is also anticipated as shown in FIG. 16 d.

Although the dimensions given are for the PDA occlusion device, it isanticipated that this device shape or modifications to it could also beused for other occlusive applications such as for ASD, VSD, PFO, or anyother similar abnormality. The central portion could alternatively bebarrel shaped, spherical, or cylindrical in outer surface with straightor tapered end walls. The central portion may be bellows shaped tofurther accommodate passage length change, double cone shaped with acenter point at the maximum diameter or any other shape as desired.Similarly the disks need not be tapered inward but this is preferred.The disks may be preformed in a non parallel manner and one disk may beof a size different from the other. Although this design is preferably 2layers it is also anticipated that additional layers (3, 4, or more) maybe used to fabricate the device. Also, the layers may be the same pickcount and the same wire diameter or they may be varied in any order ormanner as suited to a particular application. The preferred embodimentdescribed, occludes relatively quickly compared to prior art devices duethe small pore size and large surface area created by the multitude ofwires in multiple layers, has a lower profile, improved retention force,and improved conformability to adjust to a variety of vessel passagewayswith minimal interference in the native vessel flow. The reduced profileof this device is sufficiently low to allow delivery through a 4 Frenchcatheter or sheath. The device 200 is also symmetrical so that is may bedeliverable by catheter from either the pulmonary side or the aorticside as selected by the physician. The advantage of a venous approachfor PDA closure is to potentially treat infants as small a 1 kg. Theadvantage of an arterial approach in slightly larger premature infantsis that both angiography and device implant can take place from a commonaccess point in the femoral artery.

Because of the significant increase in the number of wire strands in thecomposite multi-layer structure, it is no longer necessary toincorporate a sewn-in polyester material in order to reduce the timerequired to establish total occlusion of a PDA, VSD, ASD, PFO, PVL, orother vascular location. This not only reduces the cost of manufacture,but also facilitates loading of the resulting device into a deliverycatheter of a reduced French size. Reduced French size means the abilityto treat smaller vessels which is a major advantage. This invention alsoprovides an occluder design that is more flexible, easy to track andmore adaptive to variations in the geometry of the defect whileproviding improved clamping and less intrusion into the vasculature oneither side of the defect. Over the guidewire tracking offer options fordelivery to difficult to reach anatomy. Due to device symmetry, someembodiments are deliverable from either the venous or arterial side ofthe same defect.

This invention has been described herein in considerable detail in orderto comply with the Patent Statutes and to provide those skilled in theart with the information needed to apply the novel principles and toconstruct and use embodiments of the example as required. However, it isto be understood that specifically different devices can carry out theinvention and that various modifications can be accomplished withoutdeparting from the scope of the invention itself. For example, optionsshown for one embodiment could easily be applied to other embodiments.Although many embodiments are shown as being fabricated of two braidedlayers, more layers may be added to any embodiment, as desired for aparticular application, without departing from the scope of thisinvention.

What is claimed is:
 1. A medical device for occluding a patent ductusarteriosus, the medical device comprising: at least two layers ofgenerally concentrically oriented tubular metal fabric having anexpanded preset configuration comprising proximal and distal ends,wherein the medical device comprises in the expanded presetconfiguration a proximal disk-shaped portion at the proximal end and adistal disk-shaped portion at the distal end and a central cylindricalportion disposed therebetween, each of the proximal and distaldisk-shaped portions having a maximum cross-sectional dimension largerthan the central cylindrical portion; wherein the medical device in theexpanded preset configuration further comprises a reduced diametersegment coupled to either of the proximal or distal disk-shaped portionsand the central cylindrical portion, the reduced diameter segment havinga maximum cross-sectional dimension smaller than both the proximal anddistal disk-shaped portions and the central cylindrical portion.
 2. Themedical device of claim 1, further comprising in the expanded presetconfiguration a pair of reduced diameter segments, each reduced diametersegment coupled to one of the proximal or distal disk-shaped portionsand the central cylindrical portion.
 3. The medical device of claim 2,wherein each of the reduced diameter segments has a maximumcross-sectional dimension smaller than both the proximal and distaldisk-shaped portions and the central cylindrical portion such that theproximal and distal disk-shaped portions and the central cylindricalportion are configured to pivot about an axis of the patent ductusarteriosus.
 4. The medical device of claim 1, wherein the proximal anddistal disk-shaped portions are mirror images of one another.
 5. Themedical device of claim 1, wherein each layer of tubular metal fabriccomprises a plurality of braided metal strands.
 6. The medical device ofclaim 5, wherein the metal strands comprise a material selected from thegroup consisting of stainless steel, nickel based, cobalt based,nickel-titanium, shape memory, and super-elastic materials.
 7. Themedical device of claim 6, wherein the medical device is configured tobe constrained within a catheter having an outer diameter of about 4-5French for percutaneous delivery.
 8. The medical device of claim 1,wherein the medical device is configured to be constrained within acatheter having an outer diameter of about 4-7 French for percutaneousdelivery.
 9. The medical device of claim 1, wherein at least one of theproximal and distal ends are secured by a clamp.
 10. The medical deviceof claim 9, wherein the clamp comprises a material selected from thegroup consisting of platinum-iridium and stainless steel.
 11. A deliverysystem for delivering a medical device for occluding a patent ductusarteriosus, the delivery system comprising: a delivery device coupled tothe medical device according to claim 1; and a catheter configured tooverlie the delivery device and constrain the medical device therein,wherein the medical device is configured to be deployed from thecatheter, and wherein the delivery device and catheter are configured tobe delivered to the patent ductus arteriosus and to deploy the medicaldevice at least partially within the patent ductus arteriosus.
 12. Thedelivery system of claim 11, wherein the proximal and distal disk-shapedportions are configured to be positioned outside of the patent ductusarteriosus and the central cylindrical portion is configured to bepositioned within a cavity defined by the patent ductus arteriosus. 13.The delivery system of claim 11, wherein the catheter has an outerdiameter of about 5 French.
 14. The delivery system of claim 11, whereinthe catheter has an outer diameter of about 4 French.
 15. The deliverysystem of claim 11, wherein the delivery device and catheter areconfigured to be delivered to the patent ductus arteriosus over aguidewire.
 16. The delivery system of claim 11, wherein the catheter anddelivery device are configured such that the medical device may bedeployed from the catheter in response to displacement of the catheterwith respect to the delivery device.
 17. A method for occluding a patentductus arteriosus, the method comprising: providing a medical deviceaccording to claim 1; collapsing the medical device from the presetexpanded configuration to a collapsed configuration; positioning thecollapsed medical device in a catheter; delivering the medical devicewithin the catheter to the patent ductus arteriosus; and deploying themedical device from the catheter at least partially within the patentductus arteriosus such that the medical device returns to the presetexpanded configuration.
 18. The method of claim 17, wherein deployingcomprises deploying the medical device such that the proximal and distaldisk-shaped portions are positioned outside the patent ductus arteriosusand the central cylindrical portion is positioned within a cavitydefined within the patent ductus arteriosus.
 19. The method of claim 17,wherein deploying comprises detaching a delivery system positionedwithin the catheter and coupled to the medical device.
 20. The method ofclaim 17, wherein delivering comprises delivering the medical deviceover a guide wire.